US9117439B2 - Method and apparatus for ultrasound synthetic imagining - Google Patents

Method and apparatus for ultrasound synthetic imagining Download PDF

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US9117439B2
US9117439B2 US12/047,645 US4764508A US9117439B2 US 9117439 B2 US9117439 B2 US 9117439B2 US 4764508 A US4764508 A US 4764508A US 9117439 B2 US9117439 B2 US 9117439B2
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raw data
coherent
virtual
ultrasonic
transmit focal
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US20090234230A1 (en
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Jeremy Bercoff
Claude Cohen Bacrie
Mickael Tanter
Mathias Fink
Gabriel Montaldo
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SuperSonic Imagine SA
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SuperSonic Imagine SA
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Priority to EP09153358A priority patent/EP2101191A3/en
Priority to EP21180530.4A priority patent/EP3919934A1/en
Priority to IL197306A priority patent/IL197306A/he
Priority to CA2658063A priority patent/CA2658063C/en
Priority to KR1020090021714A priority patent/KR20090098748A/ko
Priority to JP2009061469A priority patent/JP5888833B2/ja
Priority to CN2009101277453A priority patent/CN101637395B/zh
Publication of US20090234230A1 publication Critical patent/US20090234230A1/en
Priority to HK10102828.2A priority patent/HK1134645B/xx
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    • G—PHYSICS
    • G06—COMPUTING OR CALCULATING; COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T1/00—General purpose image data processing
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/18—Methods or devices for transmitting, conducting or directing sound
    • G10K11/26—Sound-focusing or directing, e.g. scanning
    • G10K11/34—Sound-focusing or directing, e.g. scanning using electrical steering of transducer arrays, e.g. beam steering
    • G10K11/341—Circuits therefor
    • G10K11/346—Circuits therefor using phase variation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8995—Combining images from different aspect angles, e.g. spatial compounding
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52046—Techniques for image enhancement involving transmitter or receiver
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S7/00—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00
    • G01S7/52—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00
    • G01S7/52017—Details of systems according to groups G01S13/00, G01S15/00, G01S17/00 of systems according to group G01S15/00 particularly adapted to short-range imaging
    • G01S7/52046—Techniques for image enhancement involving transmitter or receiver
    • G01S7/52049—Techniques for image enhancement involving transmitter or receiver using correction of medium-induced phase aberration
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8909—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration
    • G01S15/8915—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array
    • G01S15/8927—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using a static transducer configuration using a transducer array using simultaneously or sequentially two or more subarrays or subapertures
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8977—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using special techniques for image reconstruction, e.g. FFT, geometrical transformations, spatial deconvolution, time deconvolution
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
    • G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
    • G01S15/88—Sonar systems specially adapted for specific applications
    • G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
    • G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
    • G01S15/8997—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques using synthetic aperture techniques

Definitions

  • the invention relates to methods and apparatus for ultrasound synthetic imaging, in particular for medical imaging.
  • Standard ultrasound imaging consists of an insonification of the medium with a cylindrical wave that focuses on a given point.
  • a complete line of the image is computed using a dynamic receive beamforming process.
  • this procedure is repeated by sending a set of focused waves that scan along a lateral line at given depth (named the focal plane).
  • a dynamic beamforming is performed and the complete image is obtained line by line.
  • the dynamic beamforming guarantees a uniform focusing in the receive mode, whereas, in the transmit mode the focus is fixed at a given depth.
  • the final image is optimal in the focal plane and in a limited region of the medium corresponding to the focal axial length. However, outside this area which is imposed by diffraction laws, the image quality is rapidly degraded at other depths (in the near and far fields of the focused beam).
  • a classical solution is to perform multi-focus imaging: different transmit focal depths are used to obtain a homogeneous quality all over the image. Each transmission at a given focal depth enables performing a partial image in the region delimited by the axial focal length. The final image is obtained using a recombination of these partial images corresponding to various depths.
  • An optimal multi-focus image requires typically tens of focal planes. This leads to frame rate limitations, typically ⁇ 10 frames/second, that are not acceptable for ultrasound imaging. A good compromise between image quality and frame rate is around 4 focal depths images.
  • Improvement in image quality can be envisioned by performing synthetic dynamic transmit focalization.
  • Such approach consists in re-synthesizing a dynamic transmit focusing (i.e. as many focal depths as pixel in the image) by beamforming and then combining a set of different insonifications.
  • Synthetic aperture and coherent plane wave compound Two main implementations can be considered: Synthetic aperture and coherent plane wave compound.
  • the ultrasonic array is fired element by element, and the complete set of impulse responses between each transmit and receive element is beamformed and recorded, as disclosed for instance in U.S. Pat. No. 6,689,063. It is then possible to post-process these data in order to generate a synthetic image relying on both transmit and receive focusing for each pixel of the image. It has been intensely discussed in the literature whether synthetic imaging could give better images than conventional B-mode images, and how they will be affected by tissue motion and limited signal-to-noise ratio. A fundamental problem in synthetic aperture imaging is the poor signal-to-noise ratio in the images, since a single element is used for emission. This gives a much lower emitted energy compared to using the full aperture in conventional imaging and therefore limits the depth of penetration.
  • Synthetic plane wave imaging is an approach that solves at least partially the limitations of synthetic aperture imaging. It consists in transmitting plane waves of different angles in the medium, beamforming in receive the backscattered signal then combine the different image to re-synthesize to final image, as disclosed for instance in U.S. Pat. No. 6,551,246.
  • the transmission of a plane wave on the complete array generates a much higher pressure field than in the synthetic aperture approach. Moreover, diffraction and attenuation effects during propagation in soft tissues are significantly lower for an ultrasonic plane wave compared to a single element transmission.
  • Synthetic dynamic transmit focusing approaches push the boundaries of the classical Image Quality/Frame rate compromise. Optimal image qualities can be obtained at higher frame rates (>10 Hz).
  • One objective of the present invention is to propose a new synthetic ultrasound imaging method which enables to improve the past plane wave synthetic ultrasound imaging methods.
  • a method for ultrasound imaging which comprises at least the following steps:
  • the spatial coherence of the raw data is recovered at step b) prior to beamforming, thus enabling to accurately combine the data received from the transmission of the various ultrasonic waves.
  • the need to recover spatial coherence is due the fact that, when illuminating the imaged region with spatially widely spread wavefield, the echoes coming back from the medium can be seen as a wavefield originating from incoherent sources (the scatterers) randomly distributed in the imaged region: thus, the spatial coherence of the wavefield is lost (or very poor) in the raw data.
  • the beamforming may then be performed on the coherent data resulting from the coherence recovery step, thus resulting in a more accurate image.
  • Another object of the present invention is an apparatus for ultrasound imaging, comprising:
  • FIG. 1 is a schematic drawing showing a synthetic ultrasound imaging apparatus according to one embodiment of the invention
  • FIG. 2 is a block diagram showing part of the apparatus of FIG. 1 ;
  • FIG. 3 is a diagram illustrating a synthetic ultrasound imaging method which can be implemented by the apparatus of FIGS. 1 and 2 .
  • the apparatus shown on FIG. 1 is adapted for synthetic ultrasound imaging of a region 1 , for instance living tissues and in particular human tissues of a patient.
  • the apparatus may include for instance:
  • the electronic bay 3 may include for instance:
  • FIG. 3 shows one example of implementation of the method of the present invention with the apparatus of FIGS. 1 and 2 , including three main steps:
  • Step a Transmission and Data Recording
  • the transducer array is put in contact with the medium to be imaged (e.g. a patient's body), and a number N of tilted ultrasound plane waves are successively sent in the region 1 by the transducer array 2 .
  • the number N of the tilted plane waves may be comprised for instance between 2 and 100.
  • the frequency of the ultrasound waves may be comprised for instance between 0.5 and 100 MHz, for instance between 1 and 10 MHz.
  • Each tilted plane wave is characterized by the angle ⁇ of inclination of its direction of propagation with regard to axis Z (axis Z is perpendicular to the axis X of the linear transducer array 2 and defines the imaging plane with axis X).
  • Each tilted plane wave encounters a number of scatterers (speckle) and is backscattered to the transducer array 2 , so that each transducer T 1 -T n of the array receives a backscattered signal.
  • the backscattered signals of the n transducers are then respectively digitized by the analog-digital converters 5 and memorized in the n buffer memories 6 .
  • the data stored in the n buffer memories after transmission of one plane wave will be called hereafter the raw RF data.
  • the raw RF data can be considered as a matrix which is representative of the time signals received by all the transducers of the array 2 after transmission of a plane wave “RF” is a usual term in the art and just refers to the frequency of the ultrasound wave (usually in the range of 0.5 to 100 Mhz), but this expression is not limitative in any way.
  • ultrasonic plane waves could also be replaced by divergent ultrasonic waves having different propagation directions.
  • the ultrasonic waves could be spatio-temporally coded, for instance to enable a simultaneous transmission and treatment of several ultrasonic waves of different directions.
  • Step b Synthesis of Coherent RF Data
  • M coherent synthetic RF data matrices are computed using stretching time delaying and summing processes. Each one of the M computed matrices corresponds to the backscattered echoes resulting from a given virtual dynamic transmit focusing line. This may be achieved following the processes described below.
  • Substep b.1 Synthetize a First Set of Coherent RF Data Assuming a Constant Speed of Sound in the Whole Medium.
  • the total travel time gives the link between the raw RF data (RFraw (x,z, ⁇ )) and the spatially coherent RF Data (RFcoherent(x 1 ,x,z)) for the virtual transmit focus location F(x 1 ,z) considered:
  • RF ⁇ ⁇ coherent ⁇ ( x 1 , x , z ) ⁇ ⁇ ⁇ ⁇ B ⁇ ( ⁇ ) ⁇ RF ⁇ ⁇ raw ⁇ ( x , ⁇ ⁇ ( ⁇ , x 1 , x , z ) , ⁇ ) ( 4 )
  • B( ⁇ ) is a weighting function for each angle contribution.
  • a virtual focalization line is defined by all the virtual focus point F(x 1 ,z) with the same lateral position x 1 .
  • Each virtual focalization line along a given line x 1 is represented by a 2D coherent RF data matrix: the matrix RFcoherent(x 1 ,x,z).
  • M of those coherent RF data matrices are computed, M being the number of virtual transmit focalization lines that needs to be computed (i.e. for M values of x 1 ).
  • M might for example correspond to the number of transducers in the array 2 , or might be a larger number.
  • Substep b.2 Determine the Correct Focalization Laws of the Medium by Correcting the Aberrations
  • Those local aberrations may be constituted by local changes of acoustic properties such as speed of sound, density or sound absorption (In medical ultrasound, such heterogeneities exists as sound speed ranges roughly from 1460 m ⁇ s ⁇ 1 for fat to 1560 ms ⁇ 1 for muscle).
  • Such aberrations introduce errors that degrade the spatial coherency of the synthesized signal and the quality of the final ultrasound image.
  • ⁇ rew ( ⁇ , x 1 ,x,z ) ⁇ ( ⁇ , x 1 ,x,z ) (5)
  • ⁇ is the delay correction for the error induced by assuming a cylindrical focalization law.
  • the M coherent synthetic data matrices of step b.1 are the computed again using ⁇ new ( ⁇ , x 1 , x, z) as a new value of ⁇ ( ⁇ , x 1 , x, z) in formula (4).
  • phase aberration corrections are equivalent to a local estimation of the sound speed for each imaged location of the region 1 .
  • the spatial coherency of a wavefield is measured by its spatial covariance. It measures the correlation between the values of a field sensed at two points as a function of their spacing. This correlation function corresponds to the second order statistics of the spatial fluctuations of the wavefield produced by an incoherent source.
  • Van Cittert-Zernike theorem One of the major theorems of optics, the so-called Van Cittert-Zernike theorem, describes these second order statistics of such field.
  • the Van Cittert-Zernike theorem says that the spatial covariance of the field sensed at two points Xi and X 2 of an observation plane is equal to the Fourier transform of the source aperture function taken at spatial frequency (X 2 ⁇ X 1 )/ ⁇ z where ⁇ is the wavelength and z is the distance between the source and the observation plane.
  • the sharper is the incoherent source spot the larger is the area in the observation plane where the field sensed at two different points has a high similarity.
  • step b.2 may then be reiterated.
  • the number of reiterations may be predetermined, or stopping the reiterations may be subject to an error value interior to a predetermined limit.
  • Step c Receive Beamforming
  • step b) a receive beamforming is then performed on each of the M coherent RF data matrices to compute the final ultrasonic image.
  • the delay law used is the one calculated by the aberration correction method:
  • the image thus comprises M lines.
  • each one of the M computed matrices corresponds to the backscattered echoes resulting from a given virtual dynamic transmit focusing line obtained by summing over the raw per channel data for different angles ⁇ .
  • step b of the implementation it is interesting for step b of the implementation to synthesize K independent versions of the same matrix corresponding to one given line x 1 .
  • step a Another way to acquire K independent versions of the same matrix corresponding to one given line x 1 consists in modifying step a: the N tilted plane waves can be sent for successive subsets of transducers of the array (i.e. successive subapertures). Then, in step 2 , the K versions of the virtual matrix corresponding to line x 1 are built using the set of N raw RF data acquired from different subapertures of the array.
  • step b.2 The estimation of the aberrations distortions ⁇ (x 1 ,x,z) in step b.2 can then be improved as these aberrations should be the same for the K different versions of the matrix corresponding to the virtual line x 1 .
  • simply averaging ⁇ (x 1 ,x,z) for K different versions of the same matrix will reduce the variance of the estimates.
  • More complex recombinations such as DORT techniques can also be performed (see for instance: Prada C, Thomas J L. Experimental subwavelength localization of scatterers by decomposition of the time reversal operator interpreted as a covariance matrix. JOURNAL OF THE ACOUSTICAL SOCIETY OF AMERICA 114 (1): 235-243 JULY 2003, and Prada C, Manneville S, Spoliansky D, et al. Decomposition of the time reversal operator: Detection and selective focusing on two scatterers. JOURNAL OF THE ACOUSTICAL SOCIETY OF AMERICA 99 (4): 2067-2076 Part 1 April 1996).
  • the method according to the invention may be used for instance:

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Priority Applications (11)

Application Number Priority Date Filing Date Title
US12/047,645 US9117439B2 (en) 2008-03-13 2008-03-13 Method and apparatus for ultrasound synthetic imagining
EP09153358A EP2101191A3 (en) 2008-03-13 2009-02-20 Method and apparatus for ultrasound synthetic imaging
EP21180530.4A EP3919934A1 (en) 2008-03-13 2009-02-20 Method and apparatus for ultrasound synthetic imaging
IL197306A IL197306A (he) 2008-03-13 2009-02-26 שיטה ומערכת להדמית אולטראסאונד מלאכותית
CA2658063A CA2658063C (en) 2008-03-13 2009-03-11 Method and apparatus for ultrasound synthetic imaging
JP2009061469A JP5888833B2 (ja) 2008-03-13 2009-03-13 超音波合成イメージングの装置と方法
KR1020090021714A KR20090098748A (ko) 2008-03-13 2009-03-13 초음파 영상합성방법 및 그 장치
CN2009101277453A CN101637395B (zh) 2008-03-13 2009-03-13 一种用于超声波合成成像的方法和装置
HK10102828.2A HK1134645B (en) 2008-03-13 2010-03-17 Method and apparatus for ultrasound synthetic imaging
KR1020120010776A KR101529247B1 (ko) 2008-03-13 2012-02-02 초음파 영상합성방법 및 그 장치
JP2015196178A JP6030207B2 (ja) 2008-03-13 2015-10-01 超音波合成イメージングの装置と方法

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US11298110B2 (en) 2016-02-26 2022-04-12 Omar MANSOUR Doppler measurement system and method
US11619730B2 (en) * 2015-04-01 2023-04-04 Verasonics, Inc. Method and system for coded excitation imaging by impulse response estimation and retrospective acquisition

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US9282945B2 (en) 2009-04-14 2016-03-15 Maui Imaging, Inc. Calibration of ultrasound probes
US9339256B2 (en) 2007-10-01 2016-05-17 Maui Imaging, Inc. Determining material stiffness using multiple aperture ultrasound
US9788813B2 (en) 2010-10-13 2017-10-17 Maui Imaging, Inc. Multiple aperture probe internal apparatus and cable assemblies
EP2320802B1 (en) 2008-08-08 2018-08-01 Maui Imaging, Inc. Imaging with multiple aperture medical ultrasound and synchronization of add-on systems
JP5317177B2 (ja) * 2008-11-07 2013-10-16 日本電気株式会社 目標物探知装置及び目標物探知制御プログラム、目標物探知方法
JP5317176B2 (ja) * 2008-11-07 2013-10-16 日本電気株式会社 物体探査装置及び物体探査プログラム、物体探査方法
JP4776707B2 (ja) * 2009-03-30 2011-09-21 株式会社東芝 超音波画像化装置
WO2010120907A2 (en) 2009-04-14 2010-10-21 Maui Imaging, Inc. Multiple aperture ultrasound array alignment fixture
CN102076264B (zh) * 2009-04-24 2014-01-08 松下电器产业株式会社 无线超声波诊断装置、无线超声波探头以及探头认证方法
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